Wireless power receiver coil for neuromodulation device

ABSTRACT

The present disclosure relates to implantable neuromodulation devices, and in particular to a wireless power coil in a low profile environment such as with a neurostimulator. Particularly, aspects of the present disclosure are directed to a medical device that comprises a lossy housing surrounding a power supply, and a receiving coil configured to exchange power wirelessly via a wireless power transfer signal and deliver the power to the power supply. The receiving coil is adjacent the lossy housing. The receiving coil is a helical structure with a total rise that is less than or equal to a height of the lossy housing.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a Continuation of U.S. patent applicationSer. No. 16/553,866 filed Aug. 28, 2019, which claims priority andbenefit from U.S. Provisional Application No. 62/730,104, filed Sep. 12,2018, the entire contents of which are incorporated herein by referencefor all purposes.

FIELD OF THE INVENTION

The present disclosure relates to implantable neuromodulation devices,and in particular to a wireless power coil in a low profile environmentsuch as with a neurostimulator.

BACKGROUND

Normal neural activity is an intricate balance of electrical andchemical signals, which can be disrupted by a variety of insults(genetic, chemical or physical trauma) to the nervous system, causingcognitive, motor and sensory impairments. Similar to the way a cardiacpacemaker or defibrillator corrects heartbeat abnormalities,neuromodulation therapies help to reestablish normal neural balance. Inparticular instances, neuromodulation therapies utilize medical devicetechnologies to enhance or suppress activity of the nervous system forthe treatment of disease. These technologies include implantable as wellas non-implantable neuromodulation devices and systems that deliverelectrical, chemical or other agents to reversibly modify brain andnerve cell activity. The most common neuromodulation therapy is spinalcord stimulation to treat chronic neuropathic pain. In addition tochronic pain relief, some examples of neuromodulation therapies includedeep brain stimulation for essential tremor, Parkinson's disease,dystonia, epilepsy and psychiatric disorders such as depression,obsessive compulsive disorder and Tourette syndrome; sacral nervestimulation for pelvic disorders and incontinence; vagus nervestimulation for rheumatoid arthritis; gastric and colonic stimulationfor gastrointestinal disorders such as dysmotility or obesity; vagusnerve stimulation for epilepsy, obesity or depression; carotid arterystimulation for hypertension, and spinal cord stimulation for ischemicdisorders such as angina and peripheral vascular disease.

Neuromodulation devices and systems tend to have a similar form factor,derived from their predecessors, e.g. the pacemaker or defibrillator.Such neuromodulation devices and systems typically comprise an implantdevice including a neurostimulator having electronics connected to alead assembly that delivers electrical pulses to electrodes interfacedwith nerves or nerve bundles via an electrode assembly. In order tosupply energy to the neurostimulator an energy source such as anelectrochemical cell or a battery is typically arranged in theneurostimulator (e.g., within the housing of the neurostimulator).However, electrochemical cells and batteries have a limited life time.After the electrochemical cell or battery has been emptied ordischarged, it has to be re-charged or replaced when the energy storedis not sufficient for the physiological treatment. In the case of animplanted device such as a neurostimulator it is for several reasonspreferred to recharge an electrochemical cell or battery rather thanreplacing the cell or battery. One reason is the invasive natureassociated with removal and replacement of the energy source and therisk to the patient. Other reasons include that some implanted devicesconsume a relatively large amount of energy and would then have to havetheir energy sources replaced relatively often, which can beinconvenient and costly for the patient.

One of the non-invasive methods to recharge the electrochemical cell orbattery is through wireless power transfer. This method comprises anexternal power charger and a power receiver embedded into the implantdevice. The power receiver is typically made by a coil of wire connectedto power management circuitry. However, in the case of implant devicesmeant for both subcutaneous and deeper point applications, the implantdevices are typically characterized by a very low thickness profile.Given the very low thickness profile of the implant devices, the coil isoften placed next to other components such as metal enclosures forelectronic circuitry, which reduce the wireless power transferefficiency. Thus, wasting energy, requiring longer charge times and/ormore frequent charging sessions. In view of these inefficiencies, it isdesirable to develop neuromodulation devices and systems that arecapable of having design flexibility, and desirable mechanicalproperties to increase the wireless power transfer efficiency.

BRIEF SUMMARY

In various embodiments, a medical device is provided comprising: a lossyhousing surrounding a power supply; and a receiving coil configured toexchange power wirelessly via a wireless power transfer signal anddeliver the power to the power supply. The receiving coil is adjacentthe lossy housing, and the receiving coil is a helical structure with atotal rise that is less than or equal to a height of the lossy housing.

In some embodiments, the helical structure is three-dimensional and thetotal rise is determined based on a shape, a number of turns, a pitch ofeach turn, a helix length, a helix angle, or a combination thereof. Insome embodiments, the total rise is substantially the same as the heightof the lossy housing. In some embodiments, the receiving coil compriseswound wire formed from conductive material, and the conductive materialis comprised of gold (Au), gold/chromium (Au/Cr), platinum (Pt),platinum/iridium (Pt/Ir), titanium (Ti), gold/titanium (Au/Ti), or anyalloy thereof.

In some embodiments, receiving coil is within 4 mm of the lossy housing,and the lossy housing is made of a material capable of causingattenuation or dissipation of the wireless power transfer signal.

In some embodiments, the receiving coil is spaced a predetermineddistance from the lossy housing such that, during the exchange of power,a coupling factor between the receiving coil and a transmitting coil isgreater than 0.5.

In various embodiments, a medical device is provided comprising: ahousing; power supply within the housing and connected to an electronicsmodule; and a receiving coil configured to exchange power wirelessly viaa wireless power transfer signal and deliver the power to the powersupply. In some embodiments, the receiving coil is a helical structurewith a height that is determined based on a pitch between each of aplurality of turns, and at least one pitch of a turn of the plurality ofturns is different from a remainder of turns of the plurality of turns.

In some embodiments, the height is determined based on: (i) a firstpitch between a first turn and a second turn of the receiving coil; (ii)a second pitch between a last turn and a second to last turn of thereceiving coil; and (iii) a third pitch between remaining turns betweenthe second turn and the second to last turn, and wherein the at leastone pitch is the first pitch or the second pitch.

In some embodiments, the first pitch and the second pitch are less thanthe third pitch.

In some embodiments, the first pitch is the same as the second pitch.

In some embodiments, the height is determined based on: (i) a firstpitch between a first turn and a second turn of the receiving coil; (ii)a second pitch between a last turn and a second to last turn of thereceiving coil; and (iii) a third pitch between a majority of turnsbetween the second turn and the second to last turn, and wherein the atleast one pitch is the first pitch or the second pitch.

In some embodiments, the first pitch is the same as the second pitch.

In some embodiments, the first pitch and the second pitch are less thanthe third pitch.

In some embodiments, the helical structure has a shape of a roundedrectangle and includes from 4 to 15 turns.

In some embodiments, the height of the helical structure is less than orequal to a height of the lossy housing.

In various embodiments, neuromodulation system is provided comprising: atransmitting conductive structure configured to exchange powerwirelessly via a wireless power transfer signal; an implantableneurostimulator including: a lossy housing; a connector attached to ahole in the lossy housing; one or more feedthroughs that pass throughthe connector; an electronics module within the lossy housing andconnected to the one or more feedthroughs; a power supply within thelossy housing and connected to the electronics module; and a receivingconductive structure disposed outside of the housing and connected tothe power supply, wherein the receiving conductive structure isconfigured to exchange power wirelessly with the transmitting conductivestructure via the wireless power transfer signal and deliver the powerto the power supply. The receiving conductive structure is adjacent thelossy housing, and the receiving conductive structure is a helicalstructure with a total rise that is less than or equal to a height ofthe lossy housing, and a lead assembly including: a lead body includinga conductor material; a lead connector that connects the conductormaterial to the one or more feedthroughs; and one or more electrodesconnected to the conductor material.

In some embodiments, the total rise is determined based on a pitchbetween each of a plurality of turns, and wherein at least one pitch ofa turn of the plurality of turns is different from a remainder of turnsof the plurality of turns.

In some embodiments, the total rise is determined based on: (i) a firstpitch between a first turn and a second turn of the receiving coil; (ii)a second pitch between a last turn and a second to last turn of thereceiving coil; and (iii) a third pitch between remaining turns betweenthe second turn and the second to last turn, and wherein the at leastone pitch is the first pitch or the second pitch.

In some embodiments, the total rise is determined based on a helicalangle between each of a plurality of turns, and wherein at least onehelical angle of a turn of the plurality of turns is different from aremainder of helical angles of the plurality of turns.

In some embodiments, the total rise is determined based on: (i) a firsthelical angle between a first turn and a second turn of the receivingcoil; (ii) a second helical angle between a last turn and a second tolast turn of the receiving coil; and (iii) a third helical angle betweenremaining turns between the second turn and the second to last turn, andwherein the at least one helical angle is the first helical angle or thesecond helical angle.

In various embodiments, a medical device is provided that includes: alossy housing surrounding a power supply; and a receiving coilconfigured to exchange power wirelessly via a wireless power transfersignal and deliver the power to the power supply The receiving coil isspaced a predetermined distance from the lossy housing; and thepredetermined distance is determined based on: (i) a size constraint ofthe medical device, (ii) an area of the receiving coil, and (iii) acoupling factor between the receiving coil and a transmitting coil ofgreater than 0.5.

In some embodiments, the size constraint of the medical device includesa width of less than 24 mm, a height of less than 15 mm, and a length ofless than 80 mm. In some embodiments, the medical device furtherincludes a connector attached to an electronics module through a hole inthe lossy housing, and the area of the receiving coil is determinedbased on: (i) the size constraint of the medical device, (ii) a width ofthe lossy housing, (iii) a length of the connector, and (iv) thecoupling factor between the receiving coil and the transmitting coil ofgreater than 0.5.

In some embodiments, the receiving coil has a quality factor of greaterthan 50. In some embodiments, the receiving coil has a quality factor ofgreater than 100.

In some embodiments, the receiving coil is comprised gold (Au),gold/chromium (Au/Cr), platinum (Pt), platinum/iridium (Pt/Ir), titanium(Ti), gold/titanium (Au/Ti), or any alloy thereof. In some embodiments,housing is comprised of metal. Optionally, the metal is titanium or analloy thereof.

In some embodiments, the predetermined distance is from 250 μm to 6 mm.

In some embodiments, the receiving coil has a height that is determinedbased on: (i) a first pitch between a first turn and a second turn ofthe receiving coil; (ii) a second pitch between a last turn and a secondto last turn of the receiving coil; (iii) a third pitch betweenremaining turns between the second turn and the second to last turn, and(iv) a height of the medical device. In some embodiments, the receivingcoil has a width that is determined based on: (i) a width of the medicaldevice; (ii) a width of the lossy housing, and (iii) the predetermineddistance.

In some embodiments, the medical device further includes a connectorattached to an electronics module through a hole in the lossy housing.The receiving coil has a length that may be determined based on: (i) alength of the medical device; and (ii) a length of the connector. Insome embodiments, the area of the receiving coil is determined based on:(i) the height of the receiving coil, (ii) the width of the receivingcoil, (iii) the length of the receiving coil, and (iv) the couplingfactor between the receiving coil and the transmitting coil of greaterthan 0.5.

In various embodiments, a medical device is provided that includes: ahousing; power supply within the housing and connected to an electronicsmodule; and a receiving coil configured to exchange power wirelessly viaa wireless power transfer signal and deliver the power to the powersupply. The receiving coil is a helical structure with a height that isdetermined based on: (i) a first pitch between a first turn and a secondturn of the receiving coil; (ii) a second pitch between a last turn anda second to last turn of the receiving coil; and (iii) a third pitchbetween remaining turns between the second turn and the second to lastturn, and the first pitch and the second pitch are less than the thirdpitch.

In some embodiments, the medical device has a height of less than 15 mm,and the height of the receiving coil is determined based on: (i) thefirst pitch between the first turn and the second turn of the receivingcoil; (ii) the second pitch between the last turn and the second to lastturn of the receiving coil; (iii) the third pitch between remainingturns between the second turn and the second to last turn; and (iv) theheight of the medical device. In some embodiments, the height of thereceiving coil is less than or equal to the height of the medicaldevice. In some embodiments, the first pitch is from 10 μm to 3 mm, thesecond pitch is from 10 μm to 3 mm, and the third pitch is from 500 μmto 1 cm. In some embodiments, the first pitch is the same as the secondpitch. In some embodiments, the helical structure has a shape of arounded rectangle and includes from 4 to 15 turns.

In some embodiments, the receiving coil is spaced a predetermineddistance from the housing, and wherein the predetermined distance isdetermined based on: (i) a size constraint of the medical device, (ii)an area of the receiving coil, and (iii) a coupling factor between thereceiving coil and a transmitting coil of greater than 0.5.

In various embodiments, a wireless power transfer system is providedthat includes: a transmitting conductive structure configured toexchange power wirelessly via a wireless power transfer signal; and areceiving conductive structure integrated into a lossy environmentcomprising a lossy component The receiving conductive structure isconfigured to exchange power wirelessly with the transmitting conductivestructure via the wireless power transfer signal. Additionally, thereceiving conductive structure is spaced a predetermined distance fromthe lossy component; and the predetermined distance is determined basedon: (i) a size constraint of the lossy environment, (ii) an area of thereceiving coil, and (iii) a coupling factor between the receiving coiland a transmitting coil of greater than 0.5.

In some embodiments, the transmitting conductive structure and thereceiving conductive structure have a quality factor of greater than 50.In some embodiments, the transmitting conductive structure and thereceiving conductive structure have a quality factor of greater than100.

In some embodiments, the transmitting conductive structure and thereceiving conductive structure are comprised of gold (Au), gold/chromium(Au/Cr), platinum (Pt), platinum/iridium (Pt/Ir), titanium (Ti),gold/titanium (Au/Ti), or any alloy thereof. In some embodiments, thelossy component is comprised of metal. Optionally, the metal is titaniumor an alloy thereof.

In some embodiments, the predetermined distance is from 250 μm to 6 mm.

In some embodiments, the receiving conductive structure is a helicalstructure with a height that is determined based on: (i) a first pitchbetween a first turn and a second turn of the helical structure; (ii) asecond pitch between a last turn and a second to last turn of thehelical structure; (iii) a third pitch between remaining turns betweenthe second turn and the second to last turn, and (iv) a height of thelossy environment. In some embodiments, the receiving conductivestructure has a width that is determined based on: (i) a width of thelossy environment; (ii) a width of the lossy component; and (iii) thepredetermined distance.

In some embodiments, the medical device further includes a connectorattached to an electronics module through a hole in the lossy component.The receiving conductive structure has a length that may be determinedbased on: (i) a length of the lossy environment; and (ii) a length ofthe connector. In some embodiments, the area of the receiving conductivestructure is determined based on: (i) the height of the receivingconductive structure, (ii) the width of the receiving conductivestructure, (iii) the length of the receiving conductive structure, and(iv) the coupling factor between the receiving conductive structure andthe transmitting conductive structure of greater than 0.5.

In various embodiments, a neuromodulation system is provided thatincludes: a transmitting conductive structure configured to exchangepower wirelessly via a wireless power transfer signal; an implantableneurostimulator including: a lossy housing; a connector attached to ahole in the lossy housing; one or more feedthroughs that pass throughthe connector; an electronics module within the lossy housing andconnected to the one or more feedthroughs; a power supply within thelossy housing and connected to the electronics module; and a receivingconductive structure disposed outside of the housing and connected tothe power supply. The receiving conductive structure is configured toexchange power wirelessly with the transmitting conductive structure viathe wireless power transfer signal and deliver the power to the powersupply, the receiving conductive structure is spaced a predetermineddistance from the lossy housing; and the predetermined distance isdetermined based on: (i) a size constraint of the implantableneurostimulator, (ii) an area of the receiving conductive structure, and(iii) a coupling factor between the receiving conductive structure andthe transmitting conductive structure of greater than 0.5. Theneuromodulation system may further include a lead assembly including: alead body including a conductor material; a lead connector that connectsthe conductor material to the one or more feedthroughs; and one or moreelectrodes connected to the conductor material.

In some embodiments, the size constraint of the implantableneurostimulator includes a width of less than 24 mm, a height of lessthan 15 mm, and a length of less than 80 mm. In some embodiments, thearea of the receiving conductive structure is determined based on: (i)the size constraint of the implantable neurostimulator, (ii) a width ofthe lossy housing, (iii) a length of the connector, and (iv) thecoupling factor between the receiving coil and the transmitting coil ofgreater than 0.5.

In some embodiments, the transmitting conductive structure and thereceiving conductive structure have a quality factor of greater than 50.In some embodiments, the transmitting conductive structure and thereceiving conductive structure have a quality factor of greater than100.

In some embodiments, the transmitting conductive structure and thereceiving conductive structure are comprised of gold (Au), gold/chromium(Au/Cr), platinum (Pt), platinum/iridium (Pt/Ir), titanium (Ti),gold/titanium (Au/Ti), or any alloy thereof. In some embodiments, thelossy housing is comprised of metal. Optionally, the metal is titaniumor an alloy thereof.

In some embodiments, the predetermined distance is from 250 μm to 6 mm.

In some embodiments, the receiving conductive structure is a helicalstructure with a height that is determined based on: (i) a first pitchbetween a first turn and a second turn of the helical structure; (ii) asecond pitch between a last turn and a second to last turn of thehelical structure; (iii) a third pitch between remaining turns betweenthe second turn and the second to last turn, and (iv) a height of theimplantable neurostimulator. In some embodiments, the receivingconductive structure has a width that is determined based on: (i) awidth of the implantable neurostimulator; (ii) a width of the lossyhousing, and (iii) the predetermined distance. In some embodiments, thereceiving conductive structure has a length that is determined based on:(i) a length of the implantable neurostimulator; and (ii) a length ofthe connector. In some embodiments, the area of the receiving conductivestructure is determined based on: (i) the height of the receivingconductive structure, (ii) the width of the receiving conductivestructure, (iii) the length of the receiving conductive structure, and(iv) the coupling factor between the receiving conductive structure andthe transmitting conductive structure of greater than 0.5.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention will be better understood in view of the followingnon-limiting figures, in which:

FIG. 1 shows an shows a neuromodulation system in accordance withvarious embodiments;

FIG. 2 shows a wireless power transfer system in accordance with variousembodiments; and

FIGS. 3A-3F show a neurostimulator with a wireless power receiver coilin accordance with various embodiments.

DETAILED DESCRIPTION I. Introduction

The following disclosure describes a wireless power coil in a lowprofile environment such as with a neurostimulator. The basic principleof an inductively coupled power transfer system includes a transmittercoil and a receiver coil. Both coils form a system of magneticallycoupled inductors. An alternating current in the transmitter coilgenerates a magnetic field which induces a voltage in the receiver coil.By attaching a load to the receiver coil the voltage can be used topower an electronic device or charge a battery. The magnetic fieldgenerated by the transmitter coil radiates (approximately equally) inall directions, hence the flux drops rapidly with distance (obeying aninverse square law). Consequently, the receiver coil must be placed asclose as possible to the transmitter coil (less than 10 mm) to interceptthe most flux. This requirement of a close proximity between thetransmitter coil and the receiver coils is not always practical forneuromodulation therapy, especially instances in which theneurostimulator is implanted deeper than the subcutaneous layer (e.g.,within the brain or thoracic cavity).

Alternative, wireless charging systems have been developed that transferpower between a transmitter coil and a receiver coil that are operatingat identical resonant frequencies (determined by the coils' distributedcapacitance, resistance and inductance). The basic premise is that theenergy “tunnels” from one coil to the other instead of radiating in alldirections from the primary coil; and thus resonant wireless charging isnot governed by the inverse square law. This technique is still“inductive” in that the oscillating magnetic field generated by thetransmitter coil induces a current in the receiver coil and takesadvantage of the strong coupling that occurs between resonant coils evenwhen separated by tens of centimeters. Resonant wireless chargingaddresses the main drawbacks of inductive wireless charging, which isthe requirement to closely couple the coils and the demand for precisealignment from the user. However, resonant wireless charging is notwithout its own drawbacks. A primary drawback is a relatively lowefficiency due to flux leakage (even at close range a well-designedsystem might demonstrate an efficiency of 30% at 2 cm, dropping to 15%at 75 cm coil separation, greater circuit complexity and, because of the(typically) high operating frequencies, potential electromagneticinterference (EMI) challenges.

The efficiency of the power transfer in resonant wireless chargingdepends on the energy coupling rate between the coils and thecharacteristic parameters for each coil (i.e., inductor). The amount ofinductive coupling between coils is measured by their mutual inductance.The strength of the coupling may be expressed as a coupling factor,which is determined by the area of the coils including the distancebetween the coils, the ratio of width of the receiver coil/width of thetransmitter coil, the shape of the coils and the angle between thecoils. The characteristic parameters for each coil includes theresonance frequency and the intrinsic loss rate of the coils. A qualityfactor measures how well the system stores energy and is expressed asthe ratio of the resonance frequency matching between the coils and theintrinsic loss rate of the coils. A higher quality factor indicates alower rate of energy loss relative to the stored energy of the coils;the oscillations die out more slowly. Resonance allows the wirelesspower transfer system to operate at greater distances compared to anon-resonant one. However, frequency mismatch may be observed, which hasthe effect of limiting the maximum power stored and thus transferred.One factor that may influence the coupling factor and the quality factorof the coils is the external environment near the coils. In particular,the close proximity of an environmental factor such as metal or tissuehas been found to greatly influence the efficiency of the wireless powertransfer system.

Most conventional wireless power transfer systems involve transferringpower between a transmitting coil and a receiving coil in free spacewithout nearby environmental factors. Consequently, the best possibleefficiency of most conventional wireless power transmission systemsdepends on the coupling factor between the coils and the qualityfactors. However, for a low profile implanted device meant forsubcutaneous and deeper applications, the various components of theneurostimulator are packed into a tight volume of space. In a lowprofile implanted device, this means that the receiving coil will likelybe placed next to a number of environmental factors including the metalenclosure, which has been found to influence the coupling (e.g., reducethe energy available to the receiving coil due to energy absorption andchange of field shape) and the quality factor of the coils (e.g., createa frequency mismatch).

To address these limitations and problems, it has been discovered thatto improve efficiency of the wireless power transfer in a system withenvironmental factors it is important to maintain sufficient spacingbetween the coils and the environmental factors. Given a fixed area orvolume for the implantable device, maximizing the coil area to maintainsufficient coupling and keeping enough spacing to avoid the influencefrom the environmental factors means that it is important to find atradeoff between these requirements. One illustrative embodiment of thepresent disclosure is directed to a medical device that comprises alossy housing surrounding a power supply; and a receiving coilconfigured to exchange power wirelessly via a wireless power transfersignal and deliver the power to the power supply. The receiving coil isspaced a predetermined distance from the lossy housing. Thepredetermined distance is determined based on: (i) a size constraint ofthe medical device, (ii) an area of the receiving coil, and (iii) acoupling factor between the receiving coil and a transmitting coil ofgreater than 0.5.

In other embodiments, a medical device is provided comprising: ahousing; power supply within the housing and connected to an electronicsmodule; and a receiving coil configured to exchange power wirelessly viaa wireless power transfer signal and deliver the power to the powersupply. The receiving coil is a helical structure with a height that isdetermined based on: (i) a first pitch between a first turn and a secondturn of the receiving coil; (ii) a second pitch between a last turn anda second to last turn of the receiving coil; and (iii) a third pitchbetween remaining turns between the second turn and the second to lastturn. The first pitch and the second pitch are less than the thirdpitch.

In other embodiments, a wireless power transfer system is providedcomprising a transmitting conductive structure configured to exchangepower wirelessly via a wireless power transfer signal; and a receivingconductive structure integrated into a lossy environment comprising alossy component. The receiving conductive structure is configured toexchange power wirelessly with the transmitting conductive structure viathe wireless power transfer signal. The receiving conductive structureis spaced a predetermined distance from the lossy component. Thepredetermined distance is determined based on: (i) a size constraint ofthe lossy environment, (ii) an area of the receiving coil, and (iii) acoupling factor between the receiving coil and a transmitting coil ofgreater than 0.5.

In other embodiments, a neuromodulation system is provided comprising atransmitting conductive structure configured to exchange powerwirelessly via a wireless power transfer signal; an implantableneurostimulator including: a lossy housing; a connector attached to ahole in the lossy housing; one or more feedthroughs that pass throughthe connector; an electronics module within the lossy housing andconnected to the one or more feedthroughs; a power supply within thelossy housing and connected to the electronics module; and a receivingconductive structure disposed outside of the housing and connected tothe power supply. The receiving conductive structure is configured toexchange power wirelessly with the transmitting conductive structure viathe wireless power transfer signal and deliver the power to the powersupply. The receiving conductive structure is spaced a predetermineddistance from the lossy housing, and the predetermined distance isdetermined based on: (i) a size constraint of the implantableneurostimulator, (ii) an area of the receiving conductive structure, and(iii) a coupling factor between the receiving conductive structure andthe transmitting conductive structure of greater than 0.5. Theneuromodulation system further comprises a lead assembly including: alead body including a conductor material; a lead connector that connectsthe conductor material to the one or more feedthroughs; and one or moreelectrodes connected to the conductor material.

Advantageously, these approaches provide a neuromodulation system, whichhas a very low thickness profile, an efficient wireless power transfer,and greater design flexibility. More specifically, these approachesenable for spacing between the wireless power receiving coil andenvironmental factors presented by the neuromodulation system while alsomaximizing the area of the wireless power receiving coil in order tomaximize the wireless power transfer into the implanted neurostimulator.

II. Neuromodulation Devices and Systems with Wireless Power Transfer

FIG. 1 shows a neuromodulation system 100 in accordance with someaspects of the present invention. In various embodiments, theneuromodulation system 100 includes an implantable neurostimulator 105,a lead assembly 110, and a transmitting conductive structure 112 (e.g.,a transmitting coil). The implantable neurostimulator 105 may include ahousing 115, a connector 120, a power source 125, a receiving conductivestructure 130 (e.g., a wireless power coil or a receiving coil), anantenna 135, and an electronics module 140 (e.g., a computing system).The housing 115 may be comprised of materials that are biocompatiblesuch as bioceramics or bioglasses for radio frequency transparency, ormetals such as titanium or alloys thereof. In accordance with variousaspects, the size and shape of the housing 115 is selected such that theneurostimulator 105 can be implanted within a patient. In the exampleshown in FIG. 1, the connector 120 is attached to a hole in a surface ofthe housing 115 such that the housing 115 is hermetically sealed. Theconnector 120 may include one or more feedthroughs (i.e., electricallyconductive elements, pins, wires, tabs, pads, etc.) mounted within aheader and extending through the surface of the header from an interiorto an exterior of the header. The power source 125 (e.g., a battery) maybe within the housing 115 and connected (e.g., electrically connected)to the electronics module 140 to power and operate the components of theelectronics module 140. In some embodiments, the power source 125 andthe electronics module 140 are surrounded by the housing 115. Thewireless power coil 130 may be outside the housing 115 and configured toreceive electrical energy from the charging device 112. In someembodiments, the wireless power coil 130 is attached to an outsidesurface of the housing 115 by a spacer 142. The wireless power coil 130is connected (e.g., electrically connected) to the power source 125 toprovide the electrical energy to recharge or supply power to the powersource. The antenna 135 may be outside the housing 115 and connected(e.g., electrically connected) to the electronics module 140 forwireless communication with external devices via, for example,radiofrequency (RF) telemetry.

In some embodiments, the electronics module 140 may be connected (e.g.,electrically connected) to interior ends of the connector 120 such thatthe electronics module 140 is able to apply a signal or electricalcurrent to conductive traces of the lead assembly 110 connected toexterior ends of the connector 120. The electronics module 140 mayinclude discrete and/or integrated electronic circuit components thatimplement analog and/or digital circuits capable of producing thefunctions attributed to the neuromodulation devices or systems such asapplying or delivering neural stimulation to a patient. In variousembodiments, the electronics module 140 may include software and/orelectronic circuit components such as a pulse generator 145 thatgenerates a signal to deliver a voltage, current, optical, or ultrasonicstimulation to a nerve or artery/nerve plexus via electrodes, acontroller 150 that determines or senses electrical activity andphysiological responses via the electrodes and sensors, controlsstimulation parameters of the pulse generator 145 (e.g., controlstimulation parameters based on feedback from the physiologicalresponses), and/or causes delivery of the stimulation via the pulsegenerator 145 and electrodes, and a memory 155 with program instructionsoperable on by the pulse generator 145 and the controller 150 to performone or more processes for applying or delivering neural stimulation.

In various embodiments, the lead assembly 110 is a monolithic structurethat includes a cable or lead body 160. In some embodiments, the leadassembly 110 further includes one or more electrode assemblies 165having one or more electrodes 170, and optionally one or more sensors.In some embodiments, the lead assembly 110 further includes a leadconnector 175. In certain embodiments, the lead connector 175 is bondingmaterial that bonds conductor material of the lead body 160 to theelectronics module 140 of the implantable neurostimulator 105 via theconnector 120. The bonding material may be a conductive epoxy or ametallic solder or weld such as platinum. In other embodiments, the leadconnector 175 is conductive wire, conductive traces, or bond pads (e.g.,a wire, trace, or bond pads formed of a conductive material such ascopper, silver, or gold) formed on a substrate and bonds a conductor ofthe lead body 160 to the electronics module 140 of the implantableneurostimulator 105. In alternative embodiments, the implantableneurostimulator 105 and the lead body 160 are designed to connect withone another via a mechanical connector 175 such as a pin and sleeveconnector, snap and lock connector, flexible printed circuit connectors,or other means known to those of ordinary skill in the art.

The conductor material of the lead body 160 may be one or moreconductive traces 180 formed on a supporting structure 185. The one ormore conductive traces 180 allow for electrical coupling of theelectronics module 140 to the electrodes 170 and/or sensors of theelectrode assemblies 165. The supporting structure 185 may be formedwith a dielectric material such as a polymer having suitable dielectric,flexibility and biocompatibility characteristics. Polyurethane,polycarbonate, silicone, polyethylene, fluoropolymer and/or othermedical polymers, copolymers and combinations or blends may be used. Theconductive material for the traces 180 may be any suitable conductorsuch as stainless steel, silver, copper or other conductive materials,which may have separate coatings or sheathing for anticorrosive,insulative and/or protective reasons.

The electrode assemblies 165 may include the electrodes 170 and/orsensors fabricated using various shapes and patterns to create certaintypes of electrode assemblies (e.g., book electrodes, split cuffelectrodes, spiral cuff electrodes, epidural electrodes, helicalelectrodes, probe electrodes, linear electrodes, neural probe, paddleelectrodes, intraneural electrodes, etc.). In various embodiments, theelectrode assemblies 165 include a base material that provides supportfor microelectronic structures including the electrodes 170, a wiringlayer, optional contacts, etc. In some embodiments, the base material isthe supporting structure 185. The wiring layer may be embedded within orlocated on a surface of the supporting structure 185. The wiring layermay be used to electrically connect the electrodes 170 with the one ormore conductive traces 180 directly or indirectly via a lead conductor.The term “directly”, as used herein, may be defined as being withoutsomething in between. The term “indirectly”, as used herein, may bedefined as having something in between. In some embodiments, theelectrodes 170 may make electrical contact with the wiring layer byusing the contacts.

III. Wireless Power Transfer System

FIG. 2 shows a wireless power transfer system 200 comprising atransmitting device 205 and a receiving device 210 spaced apart from oneanother by a distance (D). In some embodiments, the transmitting device205 is connected to a power supply 215 such a main power line. Thetransmitting device 205 is configured to convert input power (DC or ACelectric current) from the power supply 215 into a wireless powertransfer signal 220. For example, the input power is converted into thewireless power transfer signal 220 by a first coupling device 225. Insome embodiments, the wireless power transfer signal 220 is a timevarying electromagnetic field. The receiving device 210 is configured toreceive the wireless power transfer signal 220, convert the wirelesspower transfer signal 220 into an output power (AC or DC electriccurrent), and deliver the output power to a load 230 (e.g., the powersource 125 described with respect to FIG. 1). For example, the wirelesspower transfer signal 220 is converted into the output power by a secondcoupling device 235. Accordingly, the second coupling device 235 isconfigured to exchange power wirelessly with the first coupling device225 via the wireless power transfer signal 220.

In some embodiments, the first coupling device 225 includes an optionaloscillator 240 and a transmitting conductive structure 245 (e.g., atransmitting conductive structure 112 described with respect to FIG. 1).In some embodiments, the transmitting conductive structure 245 is atransfer coil of wire configured to exchange power wirelessly via thewireless power transfer signal 220. The oscillator 240 may be used togenerate a high frequency AC current, which drives the transmittingconductive structure 245 to generate the wireless power transfer signal220 such as the time varying or oscillating electromagnetic field. Insome embodiments, the second coupling device 235 includes an optionalrectifier 250 and a receiving conductive structure 255 (e.g., areceiving conductive structure 130 described with respect to FIG. 1). Insome embodiments, the receiving conductive structure 255 is a receivingcoil of wire configured to exchange power wirelessly with thetransmitting conductive structure 245 via the wireless power transfersignal 220. The rectifier 250 may be used to convert the AC currentinduced at the receiving conductive structure 255 into DC current, whichis delivered to the load 235. In some embodiments, the transmittingconductive structure 245 and the receiving conductive structure 255 havea quality factor of greater than 50. In other embodiments, thetransmitting conductive structure 245 and the receiving conductivestructure 255 have a quality factor of greater than 100.

In some embodiments, the first coupling device 225 further includes aresonant circuit 260 which includes: (i) the transmitting conductivestructure 245 connected to a capacitor 265, (ii) the transmittingconductive structure 245 being a self-resonant coil; or (iii) anotherresonator (not shown) with internal capacitance. In some embodiments,the second coupling device 235 further includes a resonant circuit 270which includes: (i) the receiving conductive structure 255 connected toa capacitor 275, (ii) the receiving conductive structure 255 being aself-resonant coil; or (iii) another resonator (not shown) with internalcapacitance. The first coupling device 225 and the second couplingdevice 235 are tuned to resonate at a same resonant frequency. Theresonance between the transmitting conductive structure 245 and thereceiving conductive structure 255 may increase coupling and moreefficient power transfer.

In various embodiments, the receiving conductive structure 255 is in alossy environment 280. As used herein “lossy” means having or involvingthe dissipation of electrical or electromagnetic energy. A “lossy”environment is thus characterized as an environment causing theattenuation or dissipation of electrical energy. In some embodiments,the lossy environment 280 includes one or more lossy environmentalfactors or components 285, which result in current loss during thewireless power transfer between the transmitting conductive structure245 and the receiving conductive structure 255. In some embodiments, thelossy environment 280 is an implantable medical device such as aneurostimulator as described with respect to FIG. 1. In someembodiments, the one or more lossy environmental factors or components285 include body fluid, body tissue, a lossy component of theimplantable medical device, or a combination thereof. In someembodiments, the lossy component of the medical device is a housing madeof a material capable of causing attenuation or dissipation of awireless power transfer signal. In some embodiments, the material is ametal. In certain embodiments, the metal is titanium or an alloythereof.

IV. Wireless Power Coil

FIGS. 3A, 3B, and 3C show an implantable device 300 (e.g., theimplantable neurostimulator 105 described with respect to FIG. 1)comprising a receiving conductive structure 305 (e.g., the receivingconductive structure 255 described with respect to FIG. 2) in accordancewith aspects of the present disclosure. In various embodiments, a sizeof the implantable device 300 is constrained small enough such that thedevice can be implanted in a less complex and minimally invasive manner,for example, through a trocar or cannula. In some embodiments, theimplantable device 300 has a size constraint 310 including: (i) a width(w) of less than 24 mm, for example from 10 mm to 20 mm, (ii) a height(h) of less than 15 mm, for example from 5 mm to 13 mm, and (iii) alength (l) of less than 80 mm, for example from 20 mm to 40 mm. In someembodiments, the size constraint further includes a cross sectional areaof less than 190 mm², for example from 75 mm² to 160 mm². In someembodiments, the size constraint further includes a total volume of lessthan 28,800 mm³, for example from 10,000 mm³ to 20,000 mm³.

In various embodiments, the receiving conductive structure 305 isphysically configured to exchange power wirelessly via a wireless powertransfer signal and deliver the power to the power supply. Physicallyconfigured means the receiving conductive structure 305 includes: (i)inductance and power receiving capability to meet the needs of theimplantable device 200 including the ability to transfer power to thepower source with at least an 8% overall efficiency; (ii) the mechanicaldimensions (e.g., the height, width and length of the receivingconductive structure 305) fit to the size constraint 310 of theimplantable device 300; (iii) the receiving conductive structure 305 isspaced apart from environmental factors to sufficiently avoid couplingof power to the environmental factors; and (iv) the receiving conductivestructure 305 is biocompatible and a durable construction for theimplanted environment.

In some embodiments, the receiving conductive structure 305 is areceiving coil comprising wound wire. In certain embodiments, the wireis formed from a conductive material. The conductive material may becomprised of various metals or alloys thereof, for example, gold (Au),gold/chromium (Au/Cr), platinum (Pt), platinum/iridium (Pt/Ir), titanium(Ti), gold/titanium (Au/Ti), or any alloy thereof. In some embodiments,the coil has an inductance ranging from 0.5 uH to 50 uH or from 1 uH to15 uH, for example about 1.1 uH. In some embodiments, the coil has aworking frequency ranging from 1 mHz to 100 mHz or from 3 mHz to 25 mHz,for example about 6.78 mHz (ISM Standard Frequency). In someembodiments, the coil has a working voltage ranging from 5 V to 50 V orfrom 10 V to 35 V, for example about 25 V. In some embodiments, the wireof the coil has an American Wire Gauge (AWG) ranging from 25 AWG to 40AWG or from 28 AWG to 37 AWG, for example 32 AWG. As used herein, theterms “substantially,” “approximately” and “about” are defined as beinglargely but not necessarily wholly what is specified (and include whollywhat is specified) as understood by one of ordinary skill in the art. Inany disclosed embodiment, the term “substantially,” “approximately,” or“about” may be substituted with “within [a percentage] of” what isspecified, where the percentage includes 0.1, 1, 5, and 10 percent.

FIGS. 3A, 3B, and 3C show the implantable device 300 may furthercomprise a lossy housing 315 and optionally a connector 320 attached toan electronics module through a hole 322 in the lossy housing 315 (e.g.,the housing 115 and connector 120 described with respect to FIG. 1). Invarious embodiments, an epoxy covers at least a portion of theimplantable device 300 in order to hold the components together andprotect the components from environmental factors such as biologicalfluid. The epoxy may be a resin comprising one or more low molecularweight pre-polymers, one or more higher molecular weight polymers, orcombinations thereof, which comprise at least two epoxide groups. Insome embodiments, the epoxy covers substantially, if not entirely, theentire device 300 (e.g., the receiving conductive structure 305, thelossy housing 315, and the connector 320 are covered). In otherembodiments, the epoxy covers select components of the device 300 butnot all of the components (e.g., at least the receiving conductivestructure 305 and the connector 320 are covered while the lossy housingis exposed). In some embodiments, the lossy housing 315 is comprised ofmaterials that are biocompatible such as bioceramics or bioglasses forradio frequency transparency, or metals such as titanium or an alloythereof.

In various embodiments, the conductive structure 305 is adjacent to thelossy housing 315. The term “adjacent” as used herein means that onestructure is

the conductive structure 305 is spaced or within a predetermineddistance (s) from the lossy housing 315. As described herein, the lossyhousing 310 may be an environmental factor that may influenceperformance of the receiving conductive structure 305 and thus theperformance of the wireless power transfer system. In order to minimizethe influence of the lossy housing 315 on the performance of thereceiving conductive structure 305, the receiving conductive structure305 is spaced a predetermined distance (s) from the lossy housing 315.However, the predetermined distance (s) is not boundless as in freespace, and instead the predetermined distance (s) is bounded by one ormore factors including the size constraint 310 of the implantable device300, the area 325 of the receiving conductive structure 305, arequirement to minimize coupling of power from the receiving conductivestructure 305 to the housing 310, and a requirement to limit a shift inthe resonance frequency or decrease in the quality factor of thereceiving conductive structure 305. In some embodiments, thepredetermined distance (s) is determined based on: (i) the sizeconstraint 310 of the implantable device 300, (ii) the area 325 of thereceiving conductive structure 305, and (iii) a coupling factor betweenthe receiving conductive structure 305 and the transmitting conductivestructure of greater than 0.5. In some embodiments, the predetermineddistance (s) is selected such that the conductive structure 305 iswithin 4 mm of the lossy housing 315. In some embodiments, thepredetermined distance (s) is less than or equal to 4 mm, from 250 μm to4 mm, or from 500 μm to 3 mm, for example about 1 mm. As used herein,when an action is “triggered by” or “based on” something, this means theaction is triggered or based at least in part on at least a part of thesomething.

FIG. 3C shows that determining the predetermined distance (s) involves atradeoff between increasing the predetermined distance (s), whichminimizes coupling of power from the receiving conductive structure 305to the lossy housing 315, while maintaining a sufficient area 325 forthe receiving conductive structure 305 in the size constraint 310 of theimplantable device 300 to ultimately achieve a coupling factor betweenthe receiving conductive structure 305 and the transmitting conductivestructure of greater than 0.5. The coupling factor is generallydetermined by the distance (D) between the receiving conductivestructure 305 and the transmitting conductive structure and the area 325encompassed by the receiving conductive structure 305 and thetransmitting conductive structure. For example, the greater the amountof the wireless power transfer signal (e.g., the greater the amount offlux from the magnetic field) that reaches the receiving conductivestructure 305, the better the conductive structures are coupled and thehigher the coupling factor. The amount of the wireless power transfersignal that reaches the receiving conductor structure 305 may beincreased by increasing the area 325 of the receiving conductorstructure 305. However, the coupling factor may be decreased by thepresence of an environmental factor such as the housing 310, which maycouple with the receiving conductive structure 305 and leach power thatis being transferred to the receiving conductive structure 305.

As shown in FIG. 3C, the implantable device 300 has a size constraint310. In some embodiments, the size constraint 310 includes: (i) a width(w) of less than 24 mm, for example from 10 mm to 20 mm, (ii) a height(h) of less than 15 mm, for example from 5 mm to 13 mm, and (iii) alength (l) of less than 80 mm, for example from 20 mm to 40 mm. Incertain embodiments, the size constraint 310 includes a width of lessthan 24 mm, a height of less than 15 mm, and a length of less than 80mm. The receiving conductor structure 305 has area 325 defined by(w′)×(h′)×(l′). In some embodiments, the area 325 of the receivingconductor structure 305 is determined based on: (i) the size constraint310 of the implantable device 300, (ii) a width (w*) of the lossyhousing 315, (iii) optionally the length (l″) of the connector 320, and(iv) the coupling factor between the receiving conductor structure 305and the transmitting conductor structure of greater than 0.5. In someembodiments, the width (w′) is determined based on: (i) the width (w) ofthe implantable device 300; (ii) the width (w*) of the lossy housing320, and (iii) the predetermined distance (s). In some embodiments, thelength (l″) is determined based on: (i) a length (l) of the implantabledevice 300; and (ii) a length (l″) of the connector 320. In someembodiments, the height (h′) is determined based on: (i) the height (h)of the implantable device 300. Accordingly, one dimension of thetransmitting conductor structure 305 that is not determined by more thanthe size constraint 310 of the implantable device 300 is the height(h′).

In order to increase the maximum possible area 325 of the receivingconductor structure 305 to maintain the coupling factor between thereceiving conductor structure 305 and the transmitting conductorstructure of greater than 0.5 while also accommodating for thepredetermined distance (s), the height (h′) of the receiving conductorstructure 305 may be adjusted in a vertical direction. In variousembodiments, in order to increase the maximum possible area 325, thereceiving conductor structure 305 is formed in a three-dimensionalmanner rather than the conventional two-dimensional or planar coil.Testing has revealed that a three-dimensional coil is capable ofmaintaining sufficient coupling (i.e., the coupling factor between thereceiving conductor structure 305 and the transmitting conductorstructure of greater than 0.5) and power transfer with the transmittingconductor structure in such an enlarged area. In some embodiments, thereceiving conductor structure 305 is a three dimensional spiral orhelix, as shown in FIG. 3D.

The helix includes characteristics designed to maximize the area 325 ofthe receiving conductor structure 305 in view of: (i) the sizeconstraint 310 of the implantable device 300, (ii) a width (w*) of thelossy housing 315, (iii) optionally the length (l″) of the connector320, and (iv) the coupling factor between the receiving conductorstructure 305 and the transmitting conductor structure of greater than0.5. In some embodiments, the characteristics of the helix include ashape 330, a number of turns 335, a pitch 340 (rise of the helix for oneturn), a helix angle 345, a helix length 350 (a length of the coil), atotal rise 355 of the helix (overall coil height (h′)), or combinationsthereof. In some embodiments, the shape 330 of the coil is roundedrectangular. As used herein, the term “rounded rectangle” means a shapeobtained by taking the convex surface of four equal circles of radius rand placing their centers at the four corners of a rectangle with sidelengths a and b and creating a perimeter p around the surface of thefour equal circles and the rectangle, where the perimeter p of the shapeis equal to 2(a+b+πr), as shown in FIG. 3E. While the rounded rectangleshape of the coil is described herein in particular detail with respectto several described embodiments, it should be understood that othershapes of the coil have been contemplated without departing from thespirit and scope of the present invention. For example, the shape of thecoil may be square, rectangular, circular, or round, etc.

In some embodiments, the helix has a plurality of turns. In someembodiments, the helix has greater than 4 turns or from 4 to 30 turns orfrom 4 to 15 turns, for example 9 turns, and a pitch between each of theturns from 10 μm to 1 cm or from 250 μm to 2 mm, for example about 500μm. In some embodiments, the pitch between turns is the same ordifferent. In some embodiments, the helix angle is from 5° to 85°, from5° to 45°, or from 7° to 25°, for example, about 20°. In someembodiments, the helix length is from 2 cm to 100 cm or 25 cm to 75 cm,e.g., about 50 cm, from a first end 360 to a second end 365. In someembodiments, the total rise or overall coil height (h′) is less than 15mm, for example from 5 mm to 13 mm.

In various embodiments, the number of turns 335 and the helix length 350are increased to maximize the area 320 occupied by the receivingconductive structure 305. In some embodiments, the number of turns 335and the helix length 350 are increased by adjusting the pitch 340, thehelix angle 345, and the total rise 355. In some embodiments, as shownin FIG. 3F, the receiving conductor structure 305 is a helical structurewith a total rise 355 or height (h′) that is determined based on a pitchbetween each of a plurality of turns. In some embodiments, the height(h′) of the helical structure is substantially the same as a height ofthe lossy housing (e.g., height (h) of the size constraint). In someembodiments, the height (h′) of the helical structure is less than orequal to the lossy housing (e.g., height (h) of the size constraint). Insome embodiments, at least one pitch (e.g., pitch 370) of a turn (e.g.,turn 372) of the plurality of turns is different from a remainder ofturns of the plurality of turns. In some embodiments, a pitch (e.g.,pitch 370) between a first turn 372 and a second turn 375 of theplurality of turns and a pitch (e.g., pitch 380) between a last turn 382and a second to last turn 385 of the plurality of turns are the samepitch but less than a pitch (e.g., pitch 390) for a majority of turns(more than 50% of the turns between the given points) between the secondturn and the second to last turn. In some embodiments, the height (h′)is determined based on (i) a first pitch 370 between a first turn 372and a second turn 375 of the receiving conductor structure 305; (ii) asecond pitch 380 between a last turn 382 and a second to last turn 385of the receiving conductor structure 305; and (iii) a third pitch 390between remaining turns 395 between the second turn 375 and the secondto last turn 385. In certain embodiments, the first pitch 370 and/or thesecond pitch 380 are the same. In certain embodiments, the first pitch370 and/or the second pitch 380 is different from the third pitch 390.In certain embodiments, the first pitch 370 and the second pitch 380 areless than the third pitch 390.

In some embodiments, the total rise or height (h′) is determined basedon a helical angle between each of a plurality of turns. In someembodiments, at least one helical angle of a turn of the plurality ofturns is different from a remainder of helical angles of the pluralityof turns. In some embodiments, a helical angle between a first turn 372and a second turn 375 of the plurality of turns and a helical anglebetween a last turn 382 and a second to last turn 385 of the pluralityof turns are the same helical angle but less than a helical angle for amajority of turns (more than 50% of the turns between the given points)between the second turn and the second to last turn. In someembodiments, the height (h′) is determined based on (i) a first helicalangle between a first turn 372 and a second turn 375 of the receivingconductor structure 305; (ii) a second helical angle 380 between a lastturn 382 and a second to last turn 385 of the receiving conductorstructure 305; and (iii) a third helical angle 390 between remainingturns 395 between the second turn 375 and the second to last turn 385.In certain embodiments, the first helical angle and/or the secondhelical angle are the same. In certain embodiments, the first helicalangle and/or the second helical angle is different from the thirdhelical angle. In certain embodiments, the first helical angle and thesecond helical angle are less than the third helical angle.

The total rise 355 or height (h′) may be determined further based on thesize constraint 310 of the implantable device 300, in particular, theheight (h) of the implantable device 300. For example, the total rise355 or height (h′) of the receiving conductor structure 305 may bedetermined to be less than or equal to the height (h) of the implantabledevice 300. In some embodiments, the first pitch 370 and the secondpitch 380 are from 10 μm to 3 mm or from 250 μm to 2 mm, for exampleabout 500 μm; and the third pitch 390 is from 500 μm to 1 cm or from 1mm to 3 mm, for example about 2 mm. In some embodiments, the first pitch370 and the second pitch 380 are less than the third pitch 390. In someembodiments, the first pitch 370 is the same as the second pitch 380. Inother embodiments, the first pitch 370 is different from the secondpitch 380.

Accordingly, by increasing the total rise 355 or height (h′) of thereceiving conductive structure 305 and decreasing the first pitch 370and the second pitch 380 it is possible to increase the number of turns335 and the helix length 350 of the receiving conductive structure 305to maximize the area 320 occupied by the receiving conductive structure305 while maintaining the sizing constraint 310 for the implantabledevice 300 and the predetermined distance (s) between the lossy housing315 and the receiving conductive structure 305.

While the invention has been described in detail, modifications withinthe spirit and scope of the invention will be readily apparent to theskilled artisan. It should be understood that aspects of the inventionand portions of various embodiments and various features recited aboveand/or in the appended claims may be combined or interchanged either inwhole or in part. In the foregoing descriptions of the variousembodiments, those embodiments which refer to another embodiment may beappropriately combined with other embodiments as will be appreciated bythe skilled artisan. Furthermore, the skilled artisan will appreciatethat the foregoing description is by way of example only, and is notintended to limit the invention.

What is claimed is:
 1. A medical device comprising: a lossy housingsurrounding a power supply; and a receiving coil configured to exchangepower wirelessly via a wireless power transfer signal and deliver thepower to the power supply, wherein the receiving coil is spaced apredetermined distance from the lossy housing; and wherein thepredetermined distance is determined based on: (i) a size constraint ofthe medical device, (ii) an area of the receiving coil, and (iii) apredetermined strength of coupling between the receiving coil and atransmitting coil.
 2. The medical device of claim 1, the size constraintof the medical device includes a width of less than 24 mm, a height ofless than 15 mm, and a length of less than 80 mm.
 3. The medical deviceof claim 1, further comprising a connector attached to an electronicsmodule through a hole in the lossy housing, and the area of thereceiving coil is determined based on: (i) the size constraint of themedical device, (ii) a width of the lossy housing, (iii) a length of theconnector, and (iv) the predetermined strength of coupling.
 4. Themedical device of claim 1, wherein the receiving coil has a qualityfactor of greater than
 50. 5. The medical device of claim 1, wherein thereceiving coil has a quality factor of greater than
 100. 6. The medicaldevice of claim 1, wherein the receiving coil is comprised gold (Au),gold/chromium (Au/Cr), platinum (Pt), platinum/iridium (Pt/Ir), titanium(Ti), gold/titanium (Au/Ti), or any alloy thereof.
 7. The medical deviceof claim 1, wherein the housing is comprised of metal.
 8. The medicaldevice of claim 7, wherein the metal is titanium or an alloy thereof. 9.The medical device of claim 1, wherein the predetermined distance isfrom 250 μm to 6 mm.
 10. The medical device of claim 9, wherein thereceiving coil has a height that is determined based on: (i) a firstpitch between a first turn and a second turn of the receiving coil; (ii)a second pitch between a last turn and a second to last turn of thereceiving coil; (iii) a third pitch between remaining turns between thesecond turn and the second to last turn, and (iv) a height of themedical device.
 11. The medical device of claim 10, wherein thereceiving coil has a width that is determined based on: (i) a width ofthe medical device; (ii) a width of the lossy housing, and (iii) thepredetermined distance.
 12. The medical device of claim 11, furthercomprising a connector attached to an electronics module through a holein the lossy housing, wherein the receiving coil has a length that isdetermined based on: (i) a length of the medical device; and (ii) alength of the connector.
 13. The medical device of claim 12, wherein thearea of the receiving coil is determined based on: (i) the height of thereceiving coil, (ii) the width of the receiving coil, (iii) the lengthof the receiving coil, and (iv) the predetermined strength of coupling.14. A neuromodulation system comprising: a transmitting conductivestructure configured to exchange power wirelessly via a wireless powertransfer signal; an implantable neurostimulator including: a lossyhousing; a connector attached to a hole in the lossy housing; one ormore feedthroughs that pass through the connector; an electronics modulewithin the lossy housing and connected to the one or more feedthroughs;a power supply within the lossy housing and connected to the electronicsmodule; and a receiving conductive structure disposed outside of thehousing and connected to the power supply, wherein the receivingconductive structure is configured to exchange power wirelessly with thetransmitting conductive structure via the wireless power transfer signaland deliver the power to the power supply, wherein the receivingconductive structure is spaced a predetermined distance from the lossyhousing; and wherein the predetermined distance is determined based on:(i) a size constraint of the implantable neurostimulator, (ii) an areaof the receiving conductive structure, and (iii) a predeterminedstrength of coupling between the receiving coil and a transmitting coil,and a lead assembly including: a lead body including a conductormaterial; a lead connector that connects the conductor material to theone or more feedthroughs; and one or more electrodes connected to theconductor material.
 15. The neuromodulation system of claim 14, whereinthe size constraint of the implantable neurostimulator includes a widthof less than 24 mm, a height of less than 15 mm, and a length of lessthan 80 mm.
 16. The neuromodulation system of claim 14, wherein the areaof the receiving conductive structure is determined based on: (i) thesize constraint of the implantable neurostimulator, (ii) a width of thelossy housing, (iii) a length of the connector, and (iv) thepredetermined strength of coupling.
 17. The neuromodulation system ofclaim 14, wherein the transmitting conductive structure and thereceiving conductive structure have a quality factor of greater than 50.18. The neuromodulation system of claim 14, wherein the transmittingconductive structure and the receiving conductive structure have aquality factor of greater than
 100. 19. The neuromodulation system ofclaim 14, wherein the transmitting conductive structure and thereceiving conductive structure are comprised of gold (Au), gold/chromium(Au/Cr), platinum (Pt), platinum/iridium (Pt/Ir), titanium (Ti),gold/titanium (Au/Ti), or any alloy thereof.
 20. The neuromodulationsystem of claim 14, wherein the lossy housing is comprised of metal.